JP2001178674A - Endoscope and signal processing device for endoscope - Google Patents

Abstract

(57) [Summary] [Problem] Despite normal observation and fluorescence observation,
It is intended to reduce the size of the endoscope signal processing device. An endoscope signal processing device for outputting a plurality of color signal components to a monitor to display a color image of a test site on the monitor. When displaying a plurality of color signal components, the plurality of color signal components are output to a monitor as they are, and when displaying a fluorescence observation image, one of the plurality of color signal components (for example, a red signal component) is monitored. Output to

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an endoscope and an endoscope signal processing apparatus capable of obtaining an observation image by ordinary illumination light and a fluorescence image by excitation light.

[0002]

2. Description of the Related Art In recent years, autofluorescence from a living body and fluorescence of a drug administered to a living body are detected as observable images (hereinafter referred to as "fluorescence observation images"). Fluorescence observation methods for diagnosing disease states such as cancer have been proposed.

As an example of autofluorescence from a living body, for example,
NADH (nicotinamide adenine nucleotide) and F
MN (flavin mononucleotide) and the like.

As an example of a drug to be administered to a living body, H
There are fluorescent agents such as pD (hematoporphyrin) and Photofrin. Since these have accumulation properties in cancer, the disease site can be clearly recognized by fluorescence observation.

However, when the above-described fluorescence observation method is applied to an endoscope apparatus and used, the endoscope apparatus is already provided with a light source apparatus and an imaging apparatus for normal observation.
In order to perform fluorescence observation, the light source device and imaging device for normal observation must be replaced with the light source device and imaging device for fluorescence observation. This makes the replacement operation troublesome for the surgeon.

Therefore, Japanese Patent Application Laid-Open No. Hei 7-155290 proposes an invention for eliminating the troublesome replacement work. The present invention, as shown in FIG.
A reflecting mirror 102 is provided in the light source device 01 so that the illumination light from the normal observation light source device 103 and the fluorescence observation light source device 104 can be switched. Further, as a feature of the imaging means, an imaging adapter 1 of the endoscope 100 is provided.
05 is provided with a reflection mirror 106, and the normal observation camera 1
07 and the reflected light or fluorescent light to the fluorescence observation camera 108 can be switched. In addition, I.F. for opposing the imaging surface of the fluorescence observation camera 108 for light amplification of weak fluorescence is used. I. (Image intensifier) 109 is provided. Further, I. I. 10
Opposite to 9, an excitation light cut filter 110 that cuts directly reflected excitation light and transmits only fluorescent light is provided.

Then, by switching the reflecting mirrors 102 and 106 in synchronization, the light source device 10 for normal observation
When irradiating the test site 111 with normal illumination light from 3, the normal observation camera 107 captures a normal observation image, and when irradiating the test site 111 with excitation light from the fluorescent observation light source device 104, A fluorescence observation image can be captured by the fluorescence observation camera 108. The imaging signals obtained by the imaging are converted into video signals by the respective image processing devices 112 and 113 and displayed on the monitor 114.

However, in such a configuration, even if the complexity of replacement can be eliminated, the reflection mirror 106, two cameras of the normal observation camera 107 and the fluorescence observation camera 108, the excitation light cut filter 110, and the like are required. For this reason, the entire apparatus is large.

The present invention has been made in view of the above circumstances, and has as its object to reduce the size of the entire endoscope signal processing apparatus despite normal observation and fluorescence observation. .

[0010]

According to the first aspect of the present invention, a plurality of color signal components are output to the display means in order to display a color image of the test site on the display means. In the signal processing device for an endoscope, the signal processing device for the endoscope performs signal processing on the color signal component in order to switch or display simultaneously a normal observation image and a fluorescence observation image on the display means.

According to a second aspect of the present invention, there is provided an endoscope signal processing for outputting a plurality of color signal components to the display means in order to display a color image of a test site on the display means. In the device, to display a normal observation image, a signal processing unit for normal observation that outputs the plurality of color signal components to the display unit as it is, and to display a fluorescence observation image, the plurality of color signal components A signal processing means for fluorescence observation for outputting one of the signals to the display means.

According to a third aspect of the present invention, there is provided an endoscope signal processing for outputting a plurality of color signal components to the display means in order to display a color image of a test site on the display means. In the device, to display a normal observation image, a signal processing unit for normal observation that outputs the plurality of color signal components to the display unit as it is, and to display a fluorescence observation image, the plurality of color signal components A fluorescence observation signal processing unit that outputs one of the images to the display unit, and a unit that switches the normal observation image and the fluorescence observation image or simultaneously displays the image on the display unit. This is a signal processing device for an endoscope.

In the invention described in claim 4 of the present invention, the means for switching between the normal observation image and the fluorescence observation image and displaying the image on the display means performs a switching operation in synchronization with a frame identification signal. The signal processing device for an endoscope according to claim 3, characterized in that:

Further, in the invention according to claim 5 of the present invention, the means for simultaneously displaying the normal observation image and the fluorescence observation image on the display means displays each of the left and right images on the display means. The signal processing device for an endoscope according to claim 3, wherein the signal processing device performs two-screen display.

In the invention according to claim 6 of the present invention, the means for simultaneously displaying the normal observation image and the fluorescence observation image on the display means displays the two images on the display means in a superimposed manner. The signal processing device for an endoscope according to claim 3, wherein:

Further, in the invention described in claim 7 of the present invention, the display of the normal observation image and the fluorescence observation image in a superimposed manner on the display means means that one of the two images is displayed. The signal processing apparatus for an endoscope according to claim 6, wherein the display is performed in a pseudo color and the other is superimposed and displayed in a normal color.

The present invention according to claim 8 of the present invention is an endoscope for performing signal processing on an image signal obtained by imaging the test site in order to display an image of the test site on display means. A mirror signal processing device, a video signal extracting unit that extracts a video signal from the image signal, a color separation processing unit that separates the video signal into a luminance signal and a color difference signal, and a plurality of color signals from the luminance signal and the color difference signal. Conversion means for converting into components, and for displaying a normal observation image,
A signal processing unit for normal observation that outputs the plurality of color signal components converted by the conversion unit as it is to the display unit, and displays one of the plurality of color signal components to display a fluorescence observation image. And a signal processing means for fluorescence observation for outputting to the means.

Further, the invention according to claim 9 of the present invention provides:
9. The apparatus according to claim 8, wherein the color separation processing means changes spectral characteristics of red, green or blue signals after color separation by changing a matrix coefficient.
2. The signal processing device for an endoscope according to item 1.

According to a tenth aspect of the present invention, there is provided an endoscope signal processing apparatus for performing signal processing on an image signal obtained by imaging a portion to be inspected by a solid-state imaging device. An endoscope signal processing device that performs signal processing to display a fluorescence observation image using only an output from a specific color element filter among a plurality of color element filters among color filters provided on a surface. .

The invention according to claim 11 of the present invention is the signal processing device for an endoscope according to claim 10, wherein the specific color element filter is green.

Further, the invention according to claim 12 of the present invention is characterized in that the specific color element filter is a filter formed for fluorescence observation separately from normal observation. It is a signal processing device for endoscopes of an above-mentioned.

According to a thirteenth aspect of the present invention, there is provided an endoscope having a specific structure connectable to the signal processing device for an endoscope according to any one of the first to twelfth aspects. The first surface of the objective lens provided in the endoscope or the cover glass of the objective lens, provided from the light receiving surface of the solid-state imaging device that captures an image of the test site, of the excitation light, An endoscope provided with an excitation light cut filter that does not transmit a wavelength portion that generates the most noise in the red signal component by affecting a red signal component finally output to a display means. .

Here, the "first surface of the objective lens" refers to a portion of the objective lens which is closest to the test site. Further, the “wavelength portion that generates the most noise in the red signal component” refers to a half-value width of about 10 nm.

[0024] The invention according to claim 14 of the present invention is the endoscope according to claim 13, wherein the excitation light is laser light.

[0025]

DESCRIPTION OF THE PREFERRED EMBODIMENTS [First Embodiment] A first embodiment of the present invention will be described below with reference to FIGS.

FIG. 1 is a schematic view of a fluorescence endoscope apparatus 1 according to an embodiment to which the present invention is applied. The fluorescent endoscope apparatus 1 includes an electronic scope (electronic endoscope) 2 in which an illumination optical system 5 and an observation optical system 6 are disposed, and a fluorescent endoscope apparatus 1.
And a monitor 4 for displaying a normal observation image or a fluorescence observation image. Further, the processor 3 includes a light source unit 8 that supplies excitation light or illumination light to the illumination optical system 5, a signal processing unit 8 that converts an imaging signal obtained from the observation optical system 6 into a video signal, a light source unit 7, The control unit 9 controls the signal processing unit 8.

The light source unit 7 includes a white light lamp 10 typified by a Xe lamp, a reflecting mirror 11 for effectively utilizing a light beam generated from the white light lamp 10, and an illumination optical system 5.
A condenser lens 12 for condensing a light beam incident on the
A switching filter 13 for switching illumination light to be irradiated during normal observation or excitation light to be irradiated during fluorescence observation, and a motor 14 for rotating the switching filter 13 are provided.

As shown in FIG. 2, the switching filter 13 includes a normal observation filter 13a and a fluorescence observation filter 13b. Further, by rotating the center 15 as an axis in the direction of the arrow shown in FIG. 2 by driving the motor 14, the normal observation filter 13 a or the fluorescence observation filter 13 b passes through the optical path of the white light collected by the condenser lens 12. 16.

Here, the characteristics of the white light emitted from the white light lamp 10 are shown in FIG. The normal observation filter 13
a is a bandpass filter having the transmission characteristics shown in FIG. 4, and the fluorescence observation filter 13b is a bandpass filter having the transmission characteristics shown in FIG. In the figure, “relative intensity” indicates the peak of each wavelength spectrum as 1
It shows the intensity when it is set to 00, and does not show the absolute intensity.

The driving of the motor 14 shown in FIG. 1 is controlled by the control unit 9. Although the switching filter 13 is provided with the normal observation filter 13a, the opening filter may simply be formed without disposing the filter.

Next, the electronic scope 2 includes an insertion portion 17 that can be inserted into a body cavity, a grip portion 18 for an operator to grip and operate when using the electronic scope 2, and a side extending from the grip portion 18. It comprises a universal cord 19 to be output, a light source connector 21 connected to the adapter 20 of the light source unit 7, and a signal processing connector 23 connected to the adapter 22 of the signal processing unit 8.

Further, the illumination optical system 5 inside the electronic scope 2 includes a fiber bundle 24 for guiding the illumination light or the excitation light emitted from the light source unit 7 to the tip of the electronic scope 2, and the illumination light or the excitation light Illumination lens 2 for irradiating light
5. In addition, the observation optical system 6 is configured as shown in FIG.
As shown in an enlarged view in FIG. 1, the optical system includes an objective lens 26, a quartz filter 27, an optical path changing prism 28, and a CCD (charge imaging device) 29 which is a kind of solid-state imaging device.

The objective lens 26 has an outer frame formed of a lens barrel 30 in which various lenses necessary for forming a subject image on the light receiving surface of the CCD 29 are arranged.

The crystal filter 27 functions as an optical low-pass filter (optical low-pass filter) corresponding to the spatial sampling frequency of the CCD 29.

A color filter 31 of a color difference line sequential system is attached to the light receiving surface of the CCD 29. More specifically, as shown in FIG. 7, the color filter is formed in a mosaic shape by using color element filters of Mg (magenta), Cy (cyan), Ye (yellow), and G (green). FIG. 8 shows the transmittance spectrum of each color element filter. According to FIG. 8, Mg is roughly the sum of R (red) and B (blue), Cy is the sum of B and G, and Ye is R
And G.

The CCD 29 photoelectrically converts reflected light or fluorescent light from the test site and outputs the converted image signal to the signal processing unit 8. As shown in FIG. 7, in the image pickup signal output from the CCD 29, the pixel mixing line changes for each ODD / EVEN field. ODD field is ODD
, ODD2,... Are mixed and output, and the EVEN field includes EVEN1, EVEN2,.
Are mixed and output. That is, ODD
One line is output in the order of Cy + G, Ye + Mg, Cy + G,..., And the ODD2 line is Cy + Mg, Ye + G,
Cy + Mg,... Are output in this order. Also, EVEN1
The lines are output in the order of G + Cy, Mg + Ye, G + Cy,..., And the EVEN2 line is Mg + Cy, G + Ye,
Mg + Cy,... Are output in this order.

Next, the signal processing section 8 which is a characteristic part of the present embodiment will be described.

As shown in FIG. 9, the imaging signal output from the CCD 29 is a CDS (Correlated).
Double Sampling (correlated double sampling) unit 32 is transmitted. In the CDS unit 32, the CCD 2
The noise removal process for extracting a pure video signal is performed by sampling the period between the field through portion and the video portion, which is the black level of the output waveform of No. 9, and taking the difference between the two.

The video signal output from the CDS unit 32 is
The data is transmitted to the color separation processing unit 34 via the A / D converter 33. In the color separation processing section 34, the video signal is converted into luminance (Y)
The signal is separated into a signal and a color difference (RY, BY) signal. For this processing, for example, simple averaging of each pixel (addition of adjacent pixel outputs) is performed, and Y is calculated according to equations (1) to (4).
A signal is required. Note that Cy = B + G and Ye = R + G.

[0040]

(Equation 1) Here, it is calculated as an approximate signal of human visual characteristics of Y = 0.3R + 0.59G + 0.11B.

The chrominance signal is obtained from the difference between adjacent pixels, and RY output and BY output are obtained for each line.

Specifically, in the ODD1 and EVEN1 lines (lines with odd subscripts), as shown in equation (5), R
-Y signal is obtained.

[0043]

(Equation 2)

Similarly, in the ODD2 and EVEN2 lines (lines with even subscripts), BY−Y as shown in equation (6).
A signal is obtained.

[0045]

(Equation 3)

By the way, RY and BY are not output at the same time as they are. However, since the band of the color signal may be narrow due to human visual characteristics, the color difference signal on one line or the color difference signal on the upper and lower lines may be used. The interpolation (average) is a substitute. That is, RY (ODD2) = RY (ODD1) or 1/2 {RY (ODD1) + RY (ODD3)}.
BY (ODD3) = BY (ODD2)
Or 1/2 @ BY (ODD2) + BY (ODD
4) It is required in ②.

When obtaining from interpolation of upper and lower lines,
As shown in FIG. 10, this can be achieved by delaying the data of one line using the line memory 34 and performing an operation with the current line.

As described above, the Y signal and the color difference signal obtained by the color separation processing section 34 are supplied to the normal image memory 36 during normal observation by the switching operation of the switch section 35 shown in FIG.
At the time of fluorescence observation, and is stored in the fluorescence image memory 37. The video signals recorded in these are sent to the switch unit 3
5 and the switching operation of the switch unit 38 are output to the TV signal conversion unit 39.

The TV signal conversion unit 39 is provided in the normal image memory 3
5 or a video signal recorded in the fluorescent image memory 36 is converted into an NTSC signal or an RGB signal in order to display the image signal on the monitor 4 as a normal observation image or a fluorescence observation image. This TV
Since the signal converter 39 is the most characteristic part of the present embodiment, it will be described in more detail with reference to FIG.

First, a case where RGB signals are output to the monitor 4 will be described.

When the normal observation image is displayed on the monitor 4, the video signals stored in the normal image memory 36 are converted by the conversion units 40, 41, and 42 into R = Y + (RY),
B = Y + (B−Y), G = Y−0.3 / 0.59 (R−
Y) -0.11 / 0.59 (BY) are converted into R, G, and B signal components. The switch 43 operates so that the converted R, G, and B signal components (final R, G, and B signals) are output to the monitor 4. That is, the switches 43a and 43b are
1 contacts the lower contact point on the paper.

On the other hand, when the fluorescence observation image is displayed on the monitor 4, the video signals stored in the fluorescence image memory 37 are converted into R,
It is converted into G and B signal components. However, the switch 43
Operates so that all RGB outputs to the monitor 4 become R signal components. That is, the switches 43a and 43b are
Touches the upper contact on the paper.

Next, a case where an NTSC signal is output to the monitor 4 will be described.

When the normal observation image is displayed on the monitor 4, the Y signal among the video signals stored in the normal image memory 36 is not changed, and the color difference signal is quadrature-modulated by the quadrature modulation section 44 by the frequency of the color carrier. You. The switch 43 operates so that the Y signal and the orthogonally modulated color difference signal are added by the adder 45 and output to the monitor 4.

That is, the switch 43c contacts the lower contact point on the paper surface of FIG.

On the other hand, when the fluorescent observation image is displayed on the monitor 4, the color difference signal among the video signals stored in the fluorescent image
4 is quadrature modulated. However, the switch 43 operates so that the luminance component of the NTSC output to the monitor 4 is the R signal component itself and the chrominance signal is absent. That is, the switch 43c contacts the upper contact point on the paper surface of FIG.

Although the D / A converter is omitted in FIG. 11, the converters 40, 41 and 42 and the quadrature modulator 44 are used.
May be provided in a portion before input to the device, or may be provided in a portion after output. That is, the conversion units 40, 41, 42
In the quadrature modulator 44, conversion or the like may be performed with a digital signal, or conversion or the like may be performed with an analog signal.

Next, the operation of the fluorescent endoscope apparatus 1 according to the present embodiment will be described.

First, 24 hours to 36 hours before the observation by the fluorescence endoscope apparatus 1, a fluorescent agent having an accumulation property on cancer or the like is administered to the subject. When the fluorescent endoscope apparatus 1 according to the present embodiment is used, it is optimal to administer a fluorescent agent having characteristics as shown in FIG. The characteristics of this fluorescent agent are such that when irradiated with excitation light (spectrum indicated by a dotted line in FIG. 12) which is visible light having a wavelength of about 450 nm to 550 nm, directly reflected light having substantially the same wavelength is reflected, and
In FIG. 12, fluorescence having a wavelength of about 550 nm to 650 nm (a spectrum indicated by a solid line in FIG. 12) is emitted. Also,
The spectrum of the fluorescence is also included in the spectrum of the final R signal (the spectrum indicated by the thick line in FIG. 12).

Next, an operation of performing normal observation or fluorescence observation using the fluorescence endoscope apparatus 1 will be described.

First, when performing normal observation with the electronic scope 2, the operator manually operates a changeover switch (not shown) provided in the processor 3. Then, a normal display switching signal is sent from the control unit 9 shown in FIG. 1 to the light source unit 7 and the signal processing unit 8. In the light source unit 7, the motor 14 is driven such that the optical path of the white light emitted from the white light lamp 10 based on this signal passes through the normal observation filter 13a shown in FIG. The signal processing unit 8
11 in the switches 35 and 38 and the TV signal converter 39 in FIG.
Are also controlled. That is, switch 3
5 and 38 contact the upper contacts on the paper of FIG. 9 respectively, and whether the switches 43a and 43b contact the lower contacts on the paper of FIG. 11 (in the case of RGB output)
The switch 43c contacts the lower contact point on the paper surface of FIG. 11 (in the case of NTSC output).

The illumination light transmitted through the normal observation filter 13a is radiated from the illumination lens 25 to the test site via the fiber bundle 24 shown in FIG. The reflected light of the illumination light is supplied to the objective lens 26, the crystal filter 27,
An image is captured by the CCD 29 via the optical path changing prism 28 and the color filter 31.

An image signal obtained by imaging the CCD 29 is transmitted to the signal processing section 8. In the signal processing unit 8, the above-described processing is performed by the CDS unit 32, the A / D converter 33, and the color separation processing unit 34 shown in FIG. 9 and stored in the normal image memory 36 as a video signal of a normal observation image. . When displaying the normal observation image on the monitor 4, the video signal stored in the normal image memory 36 is converted into the RGB signal or the NTSC signal by the TV signal conversion unit 39 as described above,
The final color (R, G, B) signal component is displayed on the monitor 4.

On the other hand, when performing fluorescence observation with the electronic scope 2, the operator manually operates a changeover switch (not shown) provided on the processor 3. Then, a fluorescent display switching signal is sent from the control unit 9 to the light source unit 7 and the signal processing unit 8. In the light source section 7, the optical path 16 of the illumination light emitted from the white light lamp 10 based on this signal is provided.
The motor 14 is driven so that the light passes through the fluorescence observation filter 13b shown in FIG. 11 based on the switches 35 and 38 and the TV signal converter 39 shown in FIG.
Are also controlled. That is, switch 3
Whether the switches 5 and 38 contact the lower contacts on the paper of FIG. 9 respectively, and whether the switches 43a and 43b contact the upper contacts on the paper of FIG. 11 (in the case of RGB output)
The switch 43c contacts the upper contact point on the paper surface of FIG. 11 (in the case of NTSC output).

The excitation light transmitted through the fluorescence observation filter 13b is radiated through the fiber bundle 24 from the illumination lens 25 to the test site. When the test site is a cancer or the like in which the fluorescent agent accumulates, the direct reflection light of the excitation light is reflected, and the fluorescence having the wavelength spectrum shown by the thin solid line in FIG. 12 is emitted. The direct reflection light and the fluorescence of the excitation light are transmitted to the CCD 29 through the objective lens 26, the quartz filter 27, the optical path changing prism 28, and the color filter 31.
Is imaged.

An image signal obtained by imaging the CCD 29 is transmitted to the signal processing section 8. In the signal processing unit 8, C
The above-described processes are performed by the DS unit 32, the A / D converter 33, and the color separation processing unit 34, and are stored in the fluorescence image memory 37 as a video signal of a fluorescence observation image. When displaying the fluorescence observation image on the monitor 4, the video signal stored in the fluorescence image memory 37 is converted into the RGB signal or the NTSC signal by the TV signal conversion unit 39 as described above, and only the final R signal component is provided. Is output to the monitor 4. That is, conventionally, it was necessary to provide the excitation light cut filter 110 in order to substantially cut the direct reflection light of the excitation light, but in the present embodiment, the signal processing unit 8 performs signal processing to directly reflect the excitation light. Light can be cut.

As described above, since the final R signal generated by the signal processing unit 8 includes the wavelength region of the fluorescence emission spectrum, the monitor 4 displays only the final R signal component, thereby allowing the fluorescent agent to be displayed. Can be displayed.

Here, in general, since the intensity of the fluorescent light is weak compared to the intensity of the exciting light, a clear fluorescent image cannot be obtained when direct reflected light of the exciting light exists. But,
The fluorescent agent used in the present embodiment is, as shown in FIG.
Since the wavelength spectrum of the excitation light is hardly included in the wavelength spectrum of the final R signal, and the body cavity contains a red component as a main component, the component directly reflected by the excitation light is small. A clear fluorescent image can be obtained with only a signal output.

As described above, according to this embodiment, the electronic scope 2 having the color difference line sequential CCD 29 is used, and the special signal processing as described above is performed by the TV signal converter 39 of the signal processor 8. Then, by using the above-mentioned optimal fluorescent agent, the normal observation image and the fluorescence observation image can be switched and displayed on the monitor 4. Thereby, conventionally, the normal observation camera 107 and the fluorescence observation camera 108
As described above, only two cameras are required, and only one reflection mirror is not required. Therefore, the fluorescent endoscope apparatus can be downsized and the manufacturing cost can be reduced.

Further, in the present embodiment, the part which emits the fluorescent light indirectly is displayed by displaying the image relating to the final R signal instead of displaying the fluorescent light emitting the weak light directly on the monitor 4. Therefore, even if the fluorescence is weak, the monitor 4
The form such as cancer can be clearly displayed above. As a result, as in the conventional fluorescence endoscope apparatus shown in FIG. 21, an I.F. for facilitating light amplification of weak fluorescence is opposed to the imaging surface of the fluorescence observation camera 108. I. Since there is no need to provide the fluorescent endoscope 109, the size of the fluorescent endoscope apparatus can be reduced in this respect as well.

Further, the present embodiment is characterized by the signal processing unit 8 and is economical because a general electronic scope conventionally used can be used as it is.

[Second Embodiment] A second embodiment of the present invention will be described below mainly with reference to FIG.
Note that the same components as those in the first embodiment are denoted by the same reference numerals, and description thereof is omitted.

In the first embodiment, the operator manually operates a changeover switch (not shown) provided on the processor 3 to switch between normal observation and fluorescence observation.
The switching filter 13 is rotated, and the switches 35, 3
8 was also configured to be switched. On the contrary,
In this embodiment, as shown in FIG. 13, the rotation of the switching filter 13 in FIG. 2 and the switching of the switches 35 and 38 in FIG. 9 are performed in synchronization with the frame identification signal.

Specifically, the frame identification signal is used as the normal / fluorescence switching signal, and the switching filter is rotated at the frequency of the frame identification signal. Thereby, as shown in FIG.
When the frame identification signal is low, the illumination light for normal observation is illuminated, and when the frame identification signal is high, the illumination light for fluorescence observation is illuminated.

Further, since the illumination light switches in time series, the signal output from the CCD 29 also changes for each field.
It is output in order as a normal / fluorescence imaging signal. in this case,
In the present embodiment, a CCD of a CCD field accumulation type is used, and irradiation of illumination light and output of the CCD are output with a delay of one field.

The subsequent processing is the same as the processing described with reference to FIG. 9 in the first embodiment. If the frame identification signal is used for the normal / fluorescent display switching signal, the normal observation image and the fluorescence observation image are not displayed. It is displayed on the monitor 4 in a series.

The other configuration is the same as that of the first embodiment, and the description is omitted.

As described above, according to the present embodiment, it is possible to automatically display the normal observation image and the fluorescence observation image on the monitor 4. Thereby, in addition to the effect of the first embodiment, there is an effect that the operator can easily operate the fluorescence endoscope apparatus 1.

The first embodiment may be combined with the present embodiment. The normal / fluorescent light is controlled in a time series from the control of the normal / fluorescent illumination light to the input of the normal image memory 36 (or the fluorescent image memory 37). The display on the monitor 4 may be manually switched.

[Third Embodiment] A third embodiment of the present invention will be described below mainly with reference to FIG.
Note that the same components as those in the first embodiment are denoted by the same reference numerals, and description thereof is omitted.

In the first embodiment, the normal observation image and the fluorescence observation image are manually switched and displayed on the monitor 4.
In the second embodiment, the normal observation image and the fluorescence observation image are automatically and temporally switched over and displayed on the monitor 4. On the other hand, in the present embodiment, the normal observation image and the fluorescence observation image can be simultaneously displayed on two monitors on one monitor 4.

Specifically, by turning on a simultaneous display changeover switch (not shown) provided in the processor 3,
From the control unit 9 to the light source unit 7 and the signal processing unit 8
A signal (normal / fluorescent display switching signal) indicating that the normal observation image and the fluorescence observation image are to be displayed simultaneously is sent. As a result, a TV frame signal is transmitted from the signal processing unit 8 via the control unit 9, and the motor 14 rotates so that the illumination light is switched field by field based on the TV frame signal. The switching of the switch 35 is also controlled in the signal processing unit 8 so that the two image memories 3
The imaging signals obtained for each frame are written in 6, 37. The switching of the switch 38 is controlled by a 2fh signal (a signal having a frequency twice as high as the horizontal TV synchronization signal), and the memories 36 and 36 are controlled at a frequency twice as high as the horizontal TV synchronization signal.
37 outputs a video signal. Thereby, the monitor 4
The normal observation image is displayed on the left (right) half of the screen, and the fluorescence observation image is displayed on the right (left) half. The other configuration is the same as that of the first embodiment, and the description is omitted.

As described above, in this embodiment, the normal observation image and the fluorescence observation image can be displayed on two screens on the monitor 4, so that in addition to the effects of the first embodiment, the operator's diagnosis can be visually confirmed. There is an effect that simplification can be achieved from the aspect.

[Fourth Embodiment] Hereinafter, a fourth embodiment of the present invention will be described. Note that the same components as those in the first embodiment are denoted by the same reference numerals, and description thereof is omitted.

In the first embodiment, the color separation processing section 34 performs a simple color separation process. On the other hand, in the present embodiment, a matrix operation is performed on the imaging signal output from the CCD 29 as shown in Expression (7).
The matrix coefficient is switched between a normal image and a fluorescent image to a coefficient suitable for each.

[0086]

(Equation 4) Here, Y1, 2R-G, and 2B-G are the same as the color separation in the first embodiment. That is, Y1 is obtained from the addition of adjacent pixels, and 2R-G and 2BG are obtained from the difference between adjacent pixels.

Specifically, there are two types for normal observation and fluorescence observation.
RO matrix not shown beforehand
It is stored in a storage unit such as M. Of these, the coefficient data for normal observation is set to RG so as to form a normal observation image.
It outputs each signal component of B. Further, the coefficient data for the fluorescence observation is set so that the fluorescence observation image is formed.
All outputs of the GB signal components are R signal components.

Then, based on the normal / fluorescent display switching signal, it is recognized whether the observation is normal observation or fluorescence observation, and in the case of normal observation, the coefficient data for normal observation is read from the storage unit, and the fluorescence observation is performed. If, the coefficient data for fluorescence observation is read from the storage unit and the matrix coefficient is changed.

Further, in this embodiment, as shown in FIG. 15, color difference line sequential signals are synchronized by using 1H (horizontal period) delay memories 46 and 47 and an adder 48.

The other configuration is the same as that of the first embodiment, and the description is omitted.

As described above, in this embodiment, since the matrix coefficient can be changed, in addition to the effects of the first embodiment, the optimum spectral power for each image during normal observation and fluorescence observation is obtained. There is an effect that color separation of characteristics can be performed. Further, by changing the matrix coefficient, there is also an effect that the switch 43 in the first embodiment shown in FIG. 11 becomes unnecessary.

[Fifth Embodiment] A fifth embodiment of the present invention will be described below mainly with reference to FIG.
Note that the same components as those in the first embodiment are denoted by the same reference numerals, and description thereof is omitted.

In the first and second embodiments, the normal observation image and the fluorescence observation image are temporally switched and displayed on the monitor 4,
In the third embodiment, the normal observation image and the fluorescence observation image are
The screen was divided and displayed on the monitor 4 at the same time. On the other hand, in the present embodiment, the normal observation image and the fluorescence observation image are displayed on the monitor 4 simultaneously as one screen (not divided into two screens).

Specifically, when the surgeon turns on a simultaneous display changeover switch (not shown) provided in the processor 3, the control unit 9 normally sends the light source unit 7 and the signal processing unit 8 similarly to the third embodiment. A signal (normal / fluorescence display switching signal) for displaying the observation image and the fluorescence observation image simultaneously is sent. Thereby, as shown in FIG. 16, the switching of the switch 35 in the signal processing unit 9 is controlled,
An image signal obtained by normal illumination light and an image signal obtained by fluorescence excitation light are written in the two image memories 36 and 37, respectively. Then, the video signal stored in the fluorescent image memory 37 is input to the pseudo color generating section 49 to be converted into a pseudo color, and the adder 45 superimposes the video signal on the video signal stored in the normal image memory 36 to perform TV signal conversion. Output to the section.

However, in this case, the normal / fluorescent display switching signal (which is also synchronized with the rotation of the switching filter 13) has a frequency of, for example, 30 Hz, and the normal observation image and the fluorescence observation image are temporally detected by human eyes. It is necessary that it does not shift. The other configuration is the same as that of the first embodiment, and the description is omitted.

As described above, in the present embodiment, the fluorescent observation image is displayed as a pseudo color so as to be distinguishable from the color in the body cavity in the normal observation image, so that the diagnosis of the surgeon can be performed in comparison with the third embodiment. There is an effect that the visualization can be further facilitated.

[Sixth Embodiment] A sixth embodiment of the present invention will be described below. Note that the same components as those in the first embodiment are denoted by the same reference numerals, and description thereof is omitted.

In the first embodiment, each color element filter in the color filter 31 of the color difference line sequential system is pixel-mixed and output to the signal processing section 9. On the other hand, in the present embodiment, an image is formed by using only an output from a specific color element filter among the respective color element filters in the color filter 31. The fluorescent agent used is the same as that of the first embodiment.

Specifically, an image is formed using only the output from the G element filter among the color filters 31 of the color difference line sequential system. The transmittance spectrum of the G element filter is
As can be seen from FIGS. 8 and 12, the wavelength spectrum of the fluorescence emission of the optimum fluorescent agent in the first embodiment is included.

When obtaining a fluorescence observation image, an image is formed based on the emission of the fluorescence transmitted through the G element filter.
When obtaining a normal observation image, an image is formed based on reflected light transmitted through each element filter portion. In this case, the portion of the color element filter that is not used during the fluorescence observation is imaged by interpolating with the G signal.

As in the first embodiment, the wavelength spectrum of the excitation light has a characteristic that is hardly included in the wavelength spectrum of the G element filter, and the inside of the body cavity contains a red component as a main component. In addition, since the component directly reflected by the excitation light and imaged by the G element filter is small,
A clear fluorescent image can be obtained with the output of only the G element filter.

It should be noted that forming an image using only the output from a specific color element filter as in the present embodiment is not limited to the color filter 31 of the color difference line sequential system as in the present embodiment. , G and B color elements
It can also be performed with a color filter having an eyer (Bayer) arrangement.

The other configuration is the same as that of the first embodiment, and the description is omitted.

As described above, in the present embodiment, the Bayer
Since CCDs having an array of color filters can also be used, there is an effect that more types of electronic scopes can be used than in the first embodiment.

[Seventh Embodiment] Hereinafter, a seventh embodiment of the present invention will be described. Note that the same components as those in the first embodiment are denoted by the same reference numerals, and description thereof is omitted.

In the first embodiment, a color filter 31 composed of color element filters as shown in FIG.
Was used. On the other hand, in the present embodiment, a color filter 51 dedicated to the fluorescence spectrum as shown in FIG.

More specifically, the color filter 51 is provided as shown in FIG.
Of the color element filters of the color filter 31 indicated by the symbol, a part of G (green) is replaced by a K (fluorescence-only) filter that transmits a fluorescence spectrum.

When obtaining a fluorescence observation image, an image is formed based on the emission of the fluorescence transmitted through the K element filter.
When obtaining a normal observation image, the K element filter portion is interpolated with a neighboring G element filter to form an image.

The other configuration is the same as that of the first embodiment, and the description is omitted.

As described above, the present embodiment has an effect that it can be applied to an electronic scope dedicated to a fluorescence observation image.

[Eighth Embodiment] An eighth embodiment of the present invention will be described below. Note that the same components as those in the first embodiment are denoted by the same reference numerals, and description thereof is omitted.

Although the fluorescent image can be clearly displayed on the monitor 4 also in the first embodiment, this embodiment is intended to display the fluorescent image more clearly.

As shown in FIG. 12, since the final R signal contains a part of the wavelength spectrum related to the directly reflected light of the excitation light, the directly reflected light of the excitation light is detected as noise during fluorescence observation. This is not perfect for displaying a fluorescent image clearly. Therefore, in the present embodiment, FIG.
As shown in FIG. 8, the first surface (the foremost portion) of the objective lens 27
Further, a fluorescent excitation light cut filter 52 is coated by a vapor deposition method, a sputtering method, or the like.

FIG. 19 shows the spectral characteristics of the fluorescence excitation light cut filter 52. This spectral characteristic is shown in FIG.
As shown in FIG. 2, since the wavelength at which the final R signal is affected by the pumping light and noise is most generated is 520 nm, the wavelength portion (half-width at 10 nm) is cut off.

The other configuration is the same as that of the first embodiment, and the description is omitted.

As a result, the present embodiment has an effect that a fluorescent image can be displayed on the monitor 4 more clearly than in the first embodiment.

The fluorescence excitation light cut filter 52
Cuts only a small part (approximately 10 nm in half-width) of visible light, so that there is no inconvenience in that the color reproducibility of the light is hindered during normal observation.

[Ninth Embodiment] The ninth embodiment of the present invention will be described below. Note that the same components as those of the first and eighth embodiments are denoted by the same reference numerals, and description thereof is omitted.

In the first embodiment, as shown in FIG.
The configuration is such that the excitation light is irradiated by using the white light lamp 11 and the switching filter 14. On the other hand, in the present embodiment, a laser device (not shown) that can irradiate a dye laser or the like is used. In addition, the eighth aspect
The fluorescence excitation light cut filter 52 used in the embodiment is also used.

FIG. 20 shows the wavelength characteristic of the laser beam emitted from the laser device used in this embodiment by a dotted line, and the spectral characteristic of the fluorescence excitation light cut filter 52 by a solid line. As described above, in the present embodiment, the fluorescent agent is excited by using the laser light capable of outputting a single-wavelength component with high intensity to emit fluorescence, and the excitation light of the seventh embodiment generated at that time is emitted. The reflected light component and the scattered light component having a higher intensity than that of are cut by the fluorescence excitation light cut filter 52.

Thus, in the present embodiment, even if the wavelength region of the excitation light is narrowed, the fluorescent image can be displayed more clearly as in the case of the eighth embodiment. Also, in the present embodiment, similarly to the eighth embodiment, since the fluorescence excitation light cut filter 52 cuts only a small part of the visible light, the color reproducibility does not hinder the use during normal observation. There is no inconvenience.

In the eighth and ninth embodiments, regarding the formation or arrangement of the fluorescence excitation light cut filter 52,
The present invention is not limited to the first surface of the objective lens 27, and may be formed or arranged at any position between the first surface and the CCD 30 as long as the above function can be exhibited in use. In the case where a cover glass for protecting the objective lens 29 is provided further on the distal end side than the objective lens 26, the cover glass may be coated with the fluorescence excitation light cut filter 52.

The fluorescence excitation light cut filter 52 shown in the eighth and ninth embodiments is a simultaneous excitation type (white light is irradiated on a portion to be measured and reflected light is imaged by a CCD using a color filter. The method is not limited to use in a fluorescent endoscope apparatus of a type, but it is possible to sequentially irradiate a test portion with illumination light of a plane-sequential type (R, G, B) and image reflected light with a CCD that does not use a color filter. ), A clear fluorescent image equivalent to that of the simultaneous method can be obtained.

[0124]

As described above, according to the present invention,
If special signal processing is performed by the endoscope signal processing device, there is an effect that the entire device can be reduced in size although normal observation and fluorescence observation can be performed with the endoscope.

[Brief description of the drawings]

FIG. 1 is a schematic diagram of an entire fluorescence endoscope apparatus according to a first embodiment of the present invention.

FIG. 2 is an enlarged view of a switching filter according to the first embodiment of the present invention.

FIG. 3 is a diagram of a wavelength spectrum showing characteristics of white light emitted from the white light lamp according to the first embodiment of the present invention.

FIG. 4 is a diagram showing transmission characteristics of a normal observation filter.

FIG. 5 is a diagram showing transmission characteristics of a fluorescence observation filter.

FIG. 6 is an enlarged view of an observation optical system according to the first embodiment of the present invention.

FIG. 7 is a diagram illustrating a color filter according to the first embodiment of the present invention.

FIG. 8 is a diagram showing each wavelength spectrum of Mg (magenta), Cy (cyan), Ye (yellow), and G (green).

FIG. 9 is a diagram showing internal processing of a signal processing unit according to the first embodiment of the present invention.

FIG. 10 is a diagram showing internal processing of a signal processing unit according to the first embodiment of the present invention.

FIG. 11 is a diagram showing internal processing of a signal processing unit, particularly a TV signal conversion unit, according to the first embodiment of the present invention.

FIG. 12 shows wavelength spectra of excitation light, fluorescence, and a final R signal when the fluorescent endoscope apparatus and the fluorescent agent according to the first embodiment of the present invention are used.

FIG. 13 is a diagram showing internal processing of a signal processing unit according to a second embodiment of the present invention.

FIG. 14 is a diagram showing internal processing of a signal processing unit according to a third embodiment of the present invention.

FIG. 15 is a diagram showing internal processing of a signal processing unit according to a fourth embodiment of the present invention.

FIG. 16 is a diagram showing internal processing of a signal processing unit according to a fifth embodiment of the present invention.

FIG. 17 is a diagram illustrating a color filter according to a seventh embodiment of the invention.

FIG. 18 is an enlarged view of an observation optical system of an electronic scope according to an eighth embodiment of the present invention.

FIG. 19 is a diagram illustrating spectral characteristics of a fluorescence excitation light cut filter according to an eighth embodiment of the present invention.

FIG. 20 is a diagram showing a wavelength characteristic of a laser beam emitted from a laser device according to a ninth embodiment of the present invention and a spectral characteristic of a fluorescence excitation light cut filter.

FIG. 21 is a schematic view of an entire conventional fluorescence endoscope apparatus.

[Explanation of symbols]

 DESCRIPTION OF SYMBOLS 1 Fluorescence endoscope apparatus 2 Electronic scope (Electronic endoscope) 3 Processor 4 Monitor 5 Illumination optical system 6 Observation optical system 7 Light source part 8 Signal processing part 9 Control unit 10 White light lamp 11 Reflecting mirror 12 Condensing lens 13 Switching Filter 13a Filter for normal observation 13b Filter for fluorescence observation 14 Motor 15 Center of (switching filter 13) 16 Optical path of (white light) 17 Insertion part 18 Holding part 19 Universal code 20 Adapter 21 Connector for light source 22 Adapter 23 Connector for signal processing 24 Fiber Bundle 25 Illumination Lens 26 Objective Lens 27 Quartz Filter 28 Optical Path Conversion Prism 29 CCD 30 Lens Tube 31 Color Filter 32 CDS Unit 33 A / D Converter 34 Color Separation Processing Unit 35 Switch 36 Normal Image Memory 37 Fluorescent Image Memory 8 switch 39 TV signal conversion unit 40 conversion unit 41 conversion unit 42 conversion unit 43 switch 44 quadrature modulation unit 45 adder 46 1H (horizontal period) delay memory 47 1H (horizontal period) delay memory 48 adder 49 pseudo color generating unit 50 Adder 51 Color filter 52 Fluorescence excitation light cut filter

 ──────────────────────────────────────────────────続 き Continued on the front page F term (reference) 4C061 AA00 BB01 CC06 DD00 LL01 MM02 NN05 QQ04 SS09 SS21 TT13 WW04 WW08 WW10 WW17 XX02

Claims (14)

[Claims] 1. An endoscope signal processing device for outputting a plurality of color signal components to said display means in order to display a color image of a portion to be examined on said display means. A signal processing device for an endoscope that performs signal processing on the color signal components in order to switch or simultaneously display observation images. 2. An endoscope signal processing device for outputting a plurality of color signal components to said display means in order to display a color image of a portion to be examined on a display means. A signal processing unit for normal observation that outputs the plurality of color signal components as they are to the display unit; and a fluorescent light that outputs one of the plurality of color signal components to the display unit for displaying a fluorescence observation image. A signal processing device for an endoscope, comprising: signal processing means for observation. 3. An endoscope signal processing device for outputting a plurality of color signal components to said display means in order to display a color image of a portion to be examined on a display means. A signal processing unit for normal observation that outputs the plurality of color signal components as they are to the display unit; and a fluorescent light that outputs one of the plurality of color signal components to the display unit for displaying a fluorescence observation image. A signal processing device for an endoscope, comprising: a signal processing means for observation; and a means for switching between the normal observation image and the fluorescence observation image or simultaneously displaying the image on the display means. 4. A means for switching between the normal observation image and the fluorescence observation image and displaying the image on the display means in synchronization with a frame identification signal.
4. The signal processing device for an endoscope according to claim 1. 5. The means for simultaneously displaying the normal observation image and the fluorescence observation image on the display means displays two screens by displaying each of the display means on the left or right side. 4. The signal processing device for an endoscope according to 3. 6. The apparatus according to claim 3, wherein said means for simultaneously displaying said normal observation image and said fluorescence observation image on said display means superimposes and displays said two images on said display means. Endoscope signal processing device. 7. Displaying the normal observation image and the fluorescence observation image in a superimposed manner on the display means means that one of the two images is displayed in a pseudo color and the other is superimposed in a normal color. The signal processing device for an endoscope according to claim 6, wherein: 8. An endoscope signal processing device for performing signal processing on an image signal obtained by capturing an image of the test site in order to display an image of the test site on a display unit. A video signal extracting unit that extracts a signal, a color separation processing unit that separates the video signal into a luminance signal and a color difference signal, a conversion unit that converts the luminance signal and the color difference signal into a plurality of color signal components, and a normal observation image. A signal processing unit for normal observation that outputs a plurality of color signal components converted by the conversion unit to the display unit as it is for displaying; and a display unit for displaying a fluorescence observation image, among the plurality of color signal components. Signal processing means for fluorescence observation which outputs one to the display means. 9. The apparatus according to claim 8, wherein said color separation processing means is means for changing a spectral coefficient of a red, green or blue signal after color separation by changing a matrix coefficient. The signal processing device for an endoscope as described in the above. 10. A signal processing device for an endoscope that performs signal processing on an image signal obtained by imaging a portion to be inspected by a solid-state imaging device, comprising: a plurality of color filters provided on a light receiving surface of the solid-state imaging device. A signal processing device for an endoscope that performs signal processing for displaying a fluorescence observation image using only an output from a specific color element filter among color element filters. 11. The endoscope signal processing apparatus according to claim 10, wherein the specific color element filter is green. 12. The endoscope signal processing apparatus according to claim 10, wherein the specific color element filter is a filter formed for fluorescence observation separately from normal observation. 13. An endoscope having a specific structure connectable to the signal processing apparatus for an endoscope according to claim 1, wherein the endoscope is provided in the endoscope. The excitation light, which is provided between the first surface of the objective lens or the cover glass of the objective lens and the light receiving surface of the solid-state imaging device that captures an image of the test site, is finally output to the display means. An endoscope, comprising: an excitation light cut filter that does not transmit a wavelength portion that generates the most noise in the red signal component by affecting a signal component. 14. The endoscope according to claim 13, wherein the excitation light is a laser light.